US5570682A - Passive inspiratory nebulizer system - Google Patents

Passive inspiratory nebulizer system Download PDF

Info

Publication number
US5570682A
US5570682A US08166694 US16669493A US5570682A US 5570682 A US5570682 A US 5570682A US 08166694 US08166694 US 08166694 US 16669493 A US16669493 A US 16669493A US 5570682 A US5570682 A US 5570682A
Authority
US
Grant status
Grant
Patent type
Prior art keywords
gas
port
device
patient
sensor
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Expired - Fee Related
Application number
US08166694
Inventor
Robert J. Johnson
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Ethex International Inc
Original Assignee
Ethex International Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Grant date

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M11/00Sprayers or atomisers specially adapted for therapeutic purposes
    • A61M11/06Sprayers or atomisers specially adapted for therapeutic purposes of the injector type
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M15/00Inhalators
    • A61M15/0091Inhalators mechanically breath-triggered

Abstract

A hand-held nebulizer system is provided which nebulizes during the patient's inspiration cycle only. The system includes a universal sensor port adapter which is adapted to fluidly connect an airway device with a sensor port of the system's source of pressurized gas in such a manner as to permit the patient to inhale and exhale atmospheric air, while permitting the use of standard airway devices. A unique valve arrangement is also provided in the device for supplying the pressurized gas which permits the system to be extremely sensitive to small pressure differentials, thereby ensuring that the system detects the respiratory cycle phases of even the weakest patients.

Description

BACKGROUND OF THE INVENTION

This invention relates to a hand-held nebulizer system for delivering aerosolized medication to a patient, and more particularly to a passive inspiratory nebulizer system which delivers aerosolized medication only during the inspiratory phase of the patient's respiratory cycle.

Nebulization utilizes the venturi principle to fracture liquid medications into a fine aerosol mist, which a patient inhales, thereby absorbing the active ingredients of the aerosol across the pulmonary membranes to effect the desired treatment. It is a standard strategy for the therapeutic application of medicinal aerosols for a wide range of pulmonary dysfunctions, including asthma, COPD, bronchitis, cystic fibrosis, croup, etc.

One therapy employed in the respiratory care field for many years is Intermittent Positive Pressure Breathing (IPPB). This approach utilizes a machine which delivers medicated aerosols upon a patient's inspiratory effort, entrained in a stream of pressurized gas. Included in the machine is a highly sensitive control device which senses inhalation by the patient, and the resulting negative air pressure (as referenced from the ambient atmospheric pressure), causing the machine to apply a positive pressure flow of air through a T-connection or the like to a mouthpiece to assist the patient during such inhalation phase of each breathing cycle. However, to stop the stream of pressurized gas, the patient must firmly enclose the mouthpiece with his lips and positively seal the system to avoid any leakage, thus allowing pressure to build in the system, shutting it off.

Many older patients are too tired or confused to be able to cooperate in this effort, and a mask has to be fitted and firmly held over their mouth and nose, covering them. Even when sick, tired, and confused, many patients struggle. Obviously, this is not popular with either patients or practitioners.

In contrast to the IPPB approach, state of the art hand-held nebulizers, powered by pressurized gas from an outlet on the wall behind a patient's bed, or by an oilless compressor, run continuously during the entire twelve to fifteen minutes necessary to complete the medicinal nebulization prescribed for treatment of the disorder suffered by the patient.

In good health, the ratio of the time necessary for inhalation to exhalation is 1:2. That is, if it takes one second to inhale, it takes two to exhale. The essence of the dysfunction of most types of lung disease is the destruction of the structural integrity of the small airways of the lung, leading to their collapse on exhalation, and prolonging the expiratory phase of the cycle. This dysfunctional ratio may be as much as 1:4 or 1:5. Since deposition of the fresh medicinal aerosol onto the pulmonary membranes can occur only during the inspiratory phase of the respiratory cycle, nebulization during the expiratory phase is wasted, being blown into the room. While this result is obviously wasteful in terms of cost, it also makes it very difficult to ascertain how much medication is actually being received by the patient, because an unknown amount is being blown to the atmosphere during exhalation, so that the patient is unlikely to receive the exact dose prescribed by the physician.

Another alternative therapy which attempts to solve this problem is discussed in the inventor's prior U.S. Pat. No. 4,396,015. A prior art IPPB machine is employed with a modified T-connection airway device which is open to atmosphere at one end, thereby permitting the patient to inhale from and exhale to atmosphere rather than in a pressurized environment. To accomplish this, the pressurized breathing tube utilized in the IPPB system is removed, but a sensor tube between the machine and the airway device remains, so that the machine can sense the negative pressure signalling the inhalation cycle and provide pressurized gas to the nebulizer, and conversely shut off that pressurized gas when positive pressure is sensed, signalling expiration. To accomplish the desired function, the sensor tube is smaller than the diameter of the expired gas outlet port in the T-connection, so that the airway device remains open to the atmosphere.

The approach taught in the '015 patent is a vast improvement over previous prior art modalities, permitting the treatment time to be greatly shortened, and the aerosolized medication to be more accurately delivered. However, a customized T-connection airway device is required, having specific unique guide tube structure to accommodate the sensor tube. Since standardized T-connection airway devices are widely available in the industry, it is a significant disadvantage to require a customized version, both in terms of cost and availability. It is desirable, particularly in a hospital setting, to be able to stock only standardized airway devices, which are widely used, rather than to have to stock specific devices configured for only one application.

Another problem with the '015 patent approach is that the prior art IPPB machines are not sufficiently sensitive to the relatively small pressure changes generated by a sick and weak patient's respiratory cycle to reliably shut off the pressurized gas flow during the expiration cycle and to ensure that it is restored at the onset of inspiration. Accordingly, what is needed is a new driver for the passive inspiratory nebulizer system which is sensitive to extremely small pressure changes, is compact and lightweight for maximum portability, and is comprised of reliable and durable components.

SUMMARY OF THE INVENTION

This invention provides a passive inspiratory nebulization system which nebulizes during inspiration only. Since the entire goal of the hand held nebulizer modality is the inhalation of therapeutic aerosols, nebulization during the expiratory phase wastes both medication and treatment time. Nebulization during inspiration only permits a lower dosage requirement, improves patient and therapist interaction, reduces treatment time to a few well-coached breaths, and allows the clinician to titrate the medication dosage as needed.

More specifically, the invention provides a system for delivering pressurized gas during the inspiratory phase and for preventing the delivery of pressurized gas to the patient during the expiratory phase of the patient's respiratory cycle. Two particularly advantageous features distinguish the inventive system over the system disclosed in U.S. Pat. No. 4,396,015. First, a standard T-connector airway device may be employed, rather than a customized version. Second, a new pressurized gas supply device, or driver unit, is utilized, which is much more sensitive and responsive to pressure changes resulting from a patient's respiration cycle, e.g. the transition between inhalation and exhalation.

The system comprises a pressurized gas supply device, and an airway device having a first port adapted to receive pressurized gas from the gas supply device, a second port adapted to receive a mouthpiece through which a patient may inhale and exhale, and a third port which is open to the atmosphere, with a fluid passage interconnecting the first, second, and third ports. Significantly, as noted supra, the airway device may comprise a standard state of the art T-connector, which are readily available in the respiratory device market.

An important advantage of the system is the use of a universal adapter device, or sensor port adapter, for coupling the third port of the airway device to a sensor port associated with the pressurized gas supply device. The adapter device permits the device to provide pressurized gas to the first port responsive to pressure variations generated by the patient's respiration cycle. It comprises a first end adapted for insertion into the third port of the airway device and a second end adapted to be coupled to the sensor port, and further comprises structure for ensuring that the third port remains open to atmosphere when the first adapter end is inserted therein.

In another aspect of the invention, an adapter device is provided for use in an apparatus for delivering pressurized gas to a patient during inhalation and for preventing delivery of pressurized gas to the patient during exhalation. The adapter device is adapted to couple an airway device to a sensor port associated with a pressurized gas supply source, and comprises a generally tubular element having a fluid passage extending therethrough. A fluid passage extends therethrough, and the tube has a connector end adapted for insertion into an expired gas outlet port in the airway device, and a sensor end adapted to be coupled to a proximal end of a fluid line, with the fluid line being adapted to be coupled at a distal end thereof with the sensor port. Finally, and most significantly, the adapter device includes structure for ensuring that the expired gas outlet port remains open to atmosphere when the connector end is inserted therein, so that the patient is able to breathe air at atmospheric pressure at all times. Preferably, the structure comprises a generally disk-shaped element circumscribing the tubular element between the sensor end and the connector end, wherein the disk-shaped element has at least one hole extending entirely therethrough, so that when the connector end is inserted into the expired gas outlet port, the disk-shaped element abuts the end of the airway device and the airway device is open to atmosphere through the at least one hole.

Yet another important aspect of the invention is the provision of a pressurized gas supply device, which includes a fluidic valve adapted to be actuated responsive to the patient's respiratory cycle, and a gas pressure driven on/off valve adapted to be actuated responsive to a gas flow from the fluidic valve at a pressure above a predetermined trigger pressure. The on/off valve is triggered by actuation of the fluidic valve to the on position to permit the flow of pressurized gas to the airway device first port only during the patient's inspiratory cycle.

The fluidic valve includes an element which moves responsive to pressure sensed at a sensor port in the driver unit, so that when the pressure sensed at the sensor port is below a predetermined pressure, indicating that the patient is inhaling, the fluidic valve element moves responsive thereto to open the fluidic valve and permit a flow of gas at the triggering pressure to enter the on/off valve, thereby opening the on/off valve and triggering a full flow of pressurized gas to exit the driver unit for delivery to the first port in the airway device.

The invention, together with additional features and advantages thereof, may best be understood by reference to the following description taken in connection with the accompanying illustrative drawing.

BRIEF DESCRIPTION OF THE DRAWING

FIG. 1 is a schematic view of a passive inspiratory nebulizer system constructed in accordance with the teachings of the invention;

FIG. 2 is a schematic view of the interior of the driver for the passive inspiratory nebulizer system shown in FIG. 1, viewed along lines 2--2 of FIG. 1; and

FIG. 3 is a cross-sectional view of the sensor port adapter illustrated schematically in FIG. 1.

DESCRIPTION OF THE PREFERRED EMBODIMENT

FIG. 1 illustrates a passive inspiratory nebulizer system 10 which comprises a system driver unit 12 having a housing 12a, a nebulizer unit 14, and a T-connection airway device 16. The driver unit 12 includes a nebulizer port 18, which is fluidly connectable by means of a first oxygen tube 20 to the nebulizer unit 14 through a nebulizer inlet 22. The oxygen tube 20 is preferably connected to the nebulizer port 18 using a standard fitting 24 and adapter 26, and is connected to the nebulizer inlet 22 by means of a standard fitting 28. The driver unit also includes a sensor port 30, which is similarly fluidly connectable by means of a second oxygen tube 32 to the airway device 16, in a manner described more fully hereinbelow.

The T-connection 16 is an airway device, standard in the art, which is preferably molded of transparent rigid plastic. It has a first hollow tubular portion 34 and a second hollow tubular portion 36 extending at substantially right angles to one another to form a T, each of the portions 34 and 36 enclosing fluid passages (not shown) which fluidly communicate at the T intersection. The nebulizer unit 14 communicates at its outlet end with the second tubular portion 36 of the airway device 16 through a first port 38. At one end of the first tubular portion 34 is a second port 40, into which a mouthpiece 42 is adapted to be inserted. At the opposite end of the first tubular portion 34 is a third port or expired gas outlet port 44, which is open to atmosphere and into which a sensor port adapter 46 may be inserted. This expired gas outlet port 44 is provided universally in state of the art hand held nebulizer T-connection airway devices, is substantially circular, and, in the preferred embodiment, has a diameter of about 22 mm, which is also a prior art standard.

Referring now to both FIGS. 1 and 3, the sensor port adapter 46 provides an interface between the expired gas outlet port 44 and the second oxygen tube 32. It comprises a hollow tubular element 48 which has a sensor end 50 and a connector end 52. The connector end has an extruded nipple 54, hollow down its center, which is adapted to slide into a fitting 56 on the airway device end of the second oxygen tube 32, such that there is an interference fit between the nipple 54 and the fitting 56. Thus, the sensor port adapter 46 serves to interconnect the oxygen tube 32 and the sensor port adapter 46. The hollow center of the tubular element 48, in conjunction with the hollow center of the extruded nipple 54, together comprise a continuous fluid passage 58. A flat annular disk 60, preferably made of plastic, surrounds the hollow tubular element 48 and is preferably molded integrally with the cylindrical outside wall thereof, serving to separate the sensor end 50 from the connector end 52. The disk 60 actually comprises a larger diameter disk portion 62 toward the connector end side of the tube 48, which preferably has a diameter just slightly larger than the diameter of the expired gas outlet port 44 (i.e. slightly more than 22 mm in the preferred embodiment), and a smaller diameter disk portion 64, which is integral with the larger diameter portion 62, toward the sensor end side of the tube 48. The diameter of the disk portion 64, which in the preferred embodiment has a greater axial length than the disk portion 62, is sized to be slightly smaller than the diameter of the passage 58, so that the connector end 52 may be inserted into the expired gas outlet port 44 and fluid passage 58 until the smaller diameter disk portion 64 is substantially flush within the end of the passage 58 and the larger diameter disk portion 62 abuts the end of the airway device 16. The disk 58 is perforated with a plurality of holes 64, which extend completely through both disk portions 60 and 62.

At its distal end, the oxygen tube 32 is adapted to be attached to the sensor port 30. This attachment may be made in any conventional fashion, such as by means of a standard fitting 68 and threaded adapter 70, as shown in FIG. 1.

Referring now to FIG. 2, the interior of the driver 12 is illustrated. The interior 72 is preferably of a composite/plastic construction, with gas flow ducts machined appropriately therein. The exterior dimensions of the driver are designed to be as small as possible (6 in. by 4 in. by 21/2 inches in the preferred embodiment), so that the driver, being both compact and constructed of lightweight materials, is as portable as possible.

The driver 12 comprises a medical gas inlet 74, for receiving medical quality gas from a source of supply, such as a wall outlet in a hospital room. The gas, which comprises oxygen or an air mixture, is typically delivered at about 55 PSI. Once delivered through the inlet 74, the gas flows through an inlet passage 76, passing through a filter 78 to ensure its purity before being inhaled by a patient. The filter 78 is preferably a 2 micron filter, standard in the art. The gas then travels through a flow regulator 80, which regulates the trigger pressure for a pneumatically actuated on/off valve 82, in a manner to be described more fully hereinbelow.

Once it exits the regulator 80, the regulated trigger gas flows through a gas passage 84 into a first stage fluidic valve 86. The fluidic valve 86 comprises a sensor adjustment bracket 88 and a sensor yoke 90, wherein the sensor yoke 90 has a pair of upstanding legs 92 and 94, respectively. Extending downwardly and between the two yoke legs 92 and 94 is a diaphragm tip or paddle 96, which is housed within a diaphragm housing 98. The diaphragm tip 96 is adapted to be actuated upwardly or downwardly in response to fluid pressure in a sensor passage 100 which communicates with the driver sensor port 30, so that when the pressure in the passage is higher than a level determined by an adjustment of the sensor adjustment bracket 88, the diaphragm tip 96 is pushed downwardly, thereby blocking a small metering aperture (not shown) in each of the sensor yoke legs 92 and 94. On the other hand, when the pressure in the passage 100 drops below this predetermined level, the diaphragm tip is pulled upwardly, thereby unblocking the two metering apertures. In this unblocked state, the regulated trigger gas is permitted to flow through the first yoke leg 92, exit the metering aperture therein, impinge on and enter the metering aperture in the second yoke leg 94, and subsequently exit the fluidic valve 86 via a trigger gas passage 102.

The pneumatically actuated on/off valve 82 is preferably a single-stage diaphragm-actuated valve and is arranged as an in-line valve in a gas line 104, which in turn communicates at a T-fitting 106 with the fluid passage 76 upstream of the flow regulator 80. One such valve is sold under the BOOSTER-MITE trademark. The BOOSTER-MITE valve includes a gas inlet 106, a gas outlet 108, and a trigger gas inlet 110. The default condition for the valve 82 is to be shut off, so that no gas is permitted to flow from the gas passage 76 through valve inlet 106 and outlet 108 into the gas line 104. However, when gas at a pressure above a pre-determined trigger pressure enters the valve 82 through the trigger gas inlet 110, the gas pressure disrupts an established laminar gas flow, pushing that flow in another direction. This triggers a full flow of gas from the gas passage 76 through the inlet and outlet valve ports 106 and 108, respectively, and then through the gas line 104 to a flow valve 112. A flow control knob 114, actuated by either the patient or medical personnel, or perhaps even automated in some applications, controls the gas flow through the flow valve 112, which subsequently exits the driver 12 through the nebulizer outlet 18. Thus, using the control knob 114, the patient or practitioner can adjust the nebulization to the desired density.

In operation, when it is desired that a patient inhale atomized medication from the portable nebulizer unit 14, the driver unit 12 is connected to a reliable supply of medical quality gas at the gas inlet 74. The first oxygen tube 20 is interconnected between the nebulizer gas outlet 18 and the nebulizer unit inlet 22, and the second oxygen tube 32 is interconnected between the sensor port 30 and the connector end of a universal sensor port adapter 46. The sensor end of the adapter 46 is inserted into the expired gas outlet port 44 of the airway device 16, until the larger diameter disk portion 62 abuts the end of the T-tube. Then the patient inserts the mouthpiece 42 into his mouth and the nebulization process is ready to commence.

An important feature of the invention is the disk 60, which is configured so that the patient may breathe through the mouthpiece 42 and airway device 16, but is breathing air at atmospheric pressure, unlike the prior art positive pressure nebulizers. This is true because the sensor end tube 50 has a smaller diameter than that of the first tubular portion 34 and expired gas outlet port 44, so that only a small portion of the air being inhaled or exhaled by the patient flows through the tube 50. The greater portion of the inhaled and exhaled gas flows directly to or from the atmosphere through the plurality of holes 66 which are bored through the entire disk 60 and extend into the port 44, in the annular portion of the port diameter which surrounds the tube 50.

When the patient takes a breath, inhaling air through the airway device 16, including atmospheric air through the holes 66, the negative pressure generated is transmitted along the length of the second oxygen tube 32, and into the interior of the driver 12, through the sensor port 30 and the sensor passage 100. This negative pressure pulls the diaphragm tip 96, which comprises a small attached plastic block in the preferred embodiment, upwardly, thereby exposing the microscopic metering apertures in each of the yoke legs 92 and 94. This permits a microscopic flow of the triggering pressure gas from gas passage 84 to exit the first metering aperture in leg 92 and to impinge on the second metering aperture in leg 94, thereafter traveling through the trigger gas passage 102 and entering the pneumatically actuated on/off valve 82 through the trigger inlet 110. This triggers the valve 82 to open and a full flow of medical quality gas to flow from the inlet passage 76, through the valve gas inlet 106 and the gas outlet 108, and then through the gas line 104 and the flow valve 112 to the nebulizer gas outlet 18.

From the nebulizer gas outlet 18, the nebulizing gas flows through the first oxygen tube 20 and into the nebulizer unit 14, via the nebulizer unit inlet 22. This causes the nebulizer to concurrently introduce nebulized medication into the airway device 16 through the first port 38, from whence it is drawn into the patient's lungs.

During exhalation, positive air pressure is introduced into the airway device 16 as exhaled gases flow through the fluid passage 58 and outwardly to atmosphere through the holes 66 in the disk 60. The positive air pressure is sensed through the second oxygen tube 32 and the sensor port 30, creating a positive pressure in the sensor passage 100 and causing the diaphragm tip 96 to move downwardly, thereby blocking the aforementioned metering apertures in the yoke legs 92 and 94. Consequently, the cessation of trigger gas flow into the valve 82 causes the valve to switch to an off condition, thereby cutting off the flow of positive pressure gas to the nebulizer 14. This, in turn, stops the flow of nebulized medication to the patient during the balance of his or her exhalation cycle, thereby ensuring that little or no medication will be wasted into the atmosphere.

As mentioned above, another important advantage of the disclosed invention is the use of a universal sensor port adapter 46, which permits the T-connection airway device 16 to be quickly and conveniently attached to the sensor port of a driver unit, and also permits the patient to breathe atmospheric air. Because of its universality, the sensor port adapter may be interchangeably utilized with any sensing nebulizer system, and, even more importantly, may be used with standard off-the-shelf T-connector airway devices.

Yet another important advantage of the invention is the use of a fluidic valve as a first stage sensor valve which triggers a pneumatically actuated on/off valve to initiate and cut off the supply of pressurized gas to the nebulizer, responsive to the inhalation/exhalation cycle of the patient. In particular, this two stage arrangement, which employs a very low flow rate first stage fluidic valve, has a sensitivity adjustable to approximately 1/10 PSI. It is therefore adaptable even to weak, sick, older patients by use of a light aerosol mask fitted to their face, giving much less feeling of confinement and having much greater acceptance than prior art systems.

Still another important advantage of the invention is the ability it provides to accurately monitor and measure the quantity of medication actually being inhaled by the patient. In prior art nebulizers not having the feature of shutting off the flow of medication during exhalation, all of the medication nebulized and delivered during the exhalation cycle is wasted. This is costly, and also makes it difficult to determine a proper treatment regime in order to ascertain that the patient is receiving the right dosage of medication. However, when the medication is delivered only during the shorter inhalation cycle, a precise measurement of the dosage received, for instance, by using a sporometer, is easily obtained.

Of course, while the disclosed internal driver arrangement and the construction of valves 82 and 86 constitute the preferred embodiment, other arrangements and valve types capable of performing substantially the same function could be used equally effectively in the inventive system. Also, the inventive system could be packaged differently, e.g. by manifolding the tubes or re-designing the layout of the driver 12, without impacting the inventive concept.

The invention has particular applicability to hand-held nebulizers, but may also be used for a variety of other applications. For example, the inventive principles may be equally applicable to cannulas, which supply oxygen without medication, oxygen resuscitators, and perhaps insulin inhalers as well.

Although an exemplary embodiment of the invention has been shown and described, many changes, modifications, and substitutions may be made by one having ordinary skill in the art without necessarily departing from the spirit and scope of this invention. Therefore, the invention is to be limited only in accordance with the scope of the appended claims.

Claims (12)

What is claimed is:
1. A system for delivering pressurized gas to a patient during the inspiratory phase and for preventing delivery of pressurized gas to the patient during the expiratory phase of said patient's respiratory cycle, said system comprising:
a pressurized gas supply device comprising a driver unit having a housing, the housing further having disposed thereon a sensor port, a pressurized gas inlet port for receiving pressurized gas from a source of supply, and a pressurized gas outlet port;
an airway device having a first port adapted to receive pressurized gas from said supply device, a second port adapted to receive a mouthpiece through which a patient may inhale and exhale, a third port which is open to the atmosphere, and a fluid passage interconnecting said first, second, and third ports;
an adapter device for coupling said third port to said sensor port, said adapter device comprising a first end adapted for insertion into the third port and a second end adapted to be coupled to said sensor port, and further comprising structure for ensuring that said third port remains open to atmosphere when said first adapter end is inserted therein;
a fluidic valve disposed within said housing which is adapted to be actuated responsive to pressure variations in the patient's respiratory cycle, the fluidic valve including an element which moves responsive to pressure sensed at the sensor port; and
a gas pressure driven on/off valve disposed within said housing and adapted to be actuated responsive to a gas flow from said fluidic valve at a pressure above a predetermined trigger pressure, such that said on/of valve shuts off the flow of pressurized gas to said airway device during the patient's expiratory cycle;
whereby when the pressure sensed at the sensor port is relatively low, indicating that the patient is inhaling, said fluid valve element moves responsive thereto to open said fluidic valve and permit a flow of gas at said triggering pressure to enter said on/off valve, thereby opening the on/off valve and triggering a full flow of pressurized gas to exit said driver unit through the pressurized gas outlet port for delivery to the first port in said airway device.
2. A system as recited in claim 1, wherein said fluidic valve may be adjusted to respond to a pressure differential of as little as 1/10 PSI during said respiratory cycle.
3. A system as recited in claim 1, wherein said driver unit further includes a controller for regulating the rate of flow of said pressurized gas from the pressurized gas outlet port.
4. A system as recited in claim 1, and further comprising a nebulizer unit adapted to be in-line between said pressurized gas supply device and said first port, said nebulizer unit including a reservoir for containing a supply of medication and having an inlet for receiving pressurized gas from said pressurized gas supply device, and an outlet adapted for fluid communication with said first port, through which a mixture of pressurized gas and aerosolized medication may flow for inhalation by said patient.
5. A system as recited in claim 1, wherein said device is adapted to initiate the flow of pressurized gas to said first port responsive to inhalation by the patient, and to shut off the flow of pressurized gas to said first port responsive to exhalation by the patient.
6. A system as recited in claim 1, wherein said fluidic valve further comprises a sensor yoke having a pair of upstanding legs, said fluidic valve element being adapted to be actuated into a position substantially blocking fluid flow between said two legs when the pressure sensed at said pressure port is relatively high.
7. An apparatus for delivering pressurized gas to a patient during the inspiratory phase and for preventing delivery of pressurized gas to the patient during the expiratory phase of said patient's respiratory cycle, said apparatus comprising:
a pressurized gas supply device;
an airway device having a first port adapted to receive pressurized gas from said supply device, a second port adapted to receive a mouthpiece through which a patient may inhale and exhale, a third port which is open to the atmosphere, and a fluid passage interconnecting said first, second, and third ports; and
an adapter device for coupling said third port to a sensor port associated with said pressurized gas supply devices whereby said device is adapted to provide pressurized gas to said first port responsive to pressure variations generated by the patient's respiration cycle, said adapter device comprising a generally tubular element having a fluid passage therethrough and having a first end adapted for insertion into the third port and a second end adapted to be coupled to said sensor port, said first end comprising a connector end adapted for insertion into the third port, and said second end comprising a sensor end adapted to be coupled to a proximal end of a fluid line, the distal end of said fluid line being adapted to be coupled to said sensor port, such that said third port and said sensor port are in fluid communication through said generally tubular fluid passage and said fluid line;
the adapter device further including structure for ensuring that the third port remains open to atmosphere when the first adapter end is inserted therein, said structure comprising a generally disk-shaped element circumscribing said tubular element between the sensor end and the connector end, the disk-shaped element having at least one hole extending therethrough, such that when the connector end is inserted into said third port, the disk-shaped element abuts the end of the airway device and the airway device is open to the atmosphere through said at least one hole.
8. A system as recited in claim 7, wherein said disk-shaped element has a plurality of holes extending therethrough, arranged in an annular pattern surrounding said tubular element.
9. A system as recited in claim 7, wherein said disk-shaped element further comprises a first smaller diameter portion closest to the connector end of the adapter device and a second larger diameter portion closest to the sensor end of the adapter device, said at least one hole extending continuously through both of said disk diameter portions, wherein when said connector end is inserted into the airway device third port, the smaller diameter disk portion enters said airway device fluid passage while the larger diameter disk portion abuts the end of said airway device.
10. A system as recited in claim 9, wherein said first smaller diameter portion has a greater axial length than said second larger diameter portion.
11. A system as recited in claim 7, wherein said connector end is tapered for easier insertion into the proximal end of said fluid line.
12. An apparatus for delivering pressurized gas to a patient during the inspiratory phase and for preventing delivery of pressurized gas to the patient during the expiratory phase of said patient's respiratory cycle, said apparatus comprising:
a pressurized gas supply device comprising a driver unit having a housing, the housing further having disposed thereon a sensor port, a pressurized gas inlet port for receiving pressurized gas from a source of supply, and a pressurized gas outlet port;
an airway device having a first port adapted to receive pressurized gas from said supply device, a second port adapted to receive a mouthpiece through which a patient may inhale and exhale, a third port which is open to the atmosphere, and a fluid passage interconnecting said first, second, and third ports;
a fluidic valve disposed within said housing which is adapted to be actuated responsive to pressure variations in the patient's respiratory cycle, the fluidic valve including an element which moves responsive to pressure sensed at the sensor port; and
a gas pressure driven on/off valve disposed within said housing and adapted to be actuated responsive to a gas flow from said fluidic valve at a pressure above a predetermined trigger pressure, such that said on/of valve may be triggered to the on position to permit the flow of pressurized gas to the airway device first port only during the patient's inspiratory cycle;
whereby when the pressure sensed at the sensor port is relatively low, indicating that the patient is inhaling, said fluid valve element moves responsive thereto to open said fluidic valve and permit a flow of gas at said triggering pressure to enter said on/off valve, thereby opening the on/off valve and triggering a full flow of pressurized gas to exit said driver unit through the pressurized gas outlet port for delivery to the first port in said airway device.
US08166694 1993-12-14 1993-12-14 Passive inspiratory nebulizer system Expired - Fee Related US5570682A (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
US08166694 US5570682A (en) 1993-12-14 1993-12-14 Passive inspiratory nebulizer system

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US08166694 US5570682A (en) 1993-12-14 1993-12-14 Passive inspiratory nebulizer system
US08743292 US6076519A (en) 1993-12-14 1996-11-04 Passive inspiratory nebulizer system

Related Child Applications (1)

Application Number Title Priority Date Filing Date
US08743292 Division US6076519A (en) 1993-12-14 1996-11-04 Passive inspiratory nebulizer system

Publications (1)

Publication Number Publication Date
US5570682A true US5570682A (en) 1996-11-05

Family

ID=22604338

Family Applications (2)

Application Number Title Priority Date Filing Date
US08166694 Expired - Fee Related US5570682A (en) 1993-12-14 1993-12-14 Passive inspiratory nebulizer system
US08743292 Expired - Fee Related US6076519A (en) 1993-12-14 1996-11-04 Passive inspiratory nebulizer system

Family Applications After (1)

Application Number Title Priority Date Filing Date
US08743292 Expired - Fee Related US6076519A (en) 1993-12-14 1996-11-04 Passive inspiratory nebulizer system

Country Status (1)

Country Link
US (2) US5570682A (en)

Cited By (116)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5699786A (en) * 1995-10-31 1997-12-23 Sanyo Electric Co., Ltd. Atomizer system
WO1998025662A1 (en) * 1996-12-12 1998-06-18 Resmed Limited Substance delivery in breathable gas supply system
WO1999026004A1 (en) 1997-11-14 1999-05-27 Salter Labs Pilot valve
EP0855224A3 (en) * 1997-01-27 1999-07-07 Medic-Aid Limited Atomizer
US6006748A (en) 1996-10-16 1999-12-28 Resmed Limited Vent valve apparatus
US6029665A (en) 1993-11-05 2000-02-29 Resmed Limited Determination of patency of airway
USD421298S (en) 1998-04-23 2000-02-29 Resmed Limited Flow generator
US6041776A (en) * 1998-05-14 2000-03-28 Briggs, Iii; Stephen W. Medical nebulization device
US6044844A (en) 1996-12-02 2000-04-04 Resmed Limited Mask and harness assembly
US6076520A (en) * 1997-05-12 2000-06-20 Cooper; Emily L. Device for nasal therapeutic inhalation
US6076519A (en) * 1993-12-14 2000-06-20 Ethex International, Inc. Passive inspiratory nebulizer system
US6091973A (en) 1995-04-11 2000-07-18 Resmed Limited Monitoring the occurrence of apneic and hypopneic arousals
US6112746A (en) 1996-07-26 2000-09-05 Resmed Limited Nasal mask and mask cushion therefor
US6119723A (en) 1997-02-14 2000-09-19 Resmed Limited, Apparatus for varying the flow area of a conduit
US6119693A (en) 1998-01-16 2000-09-19 Resmed Limited Forehead support for facial mask
US6123071A (en) 1993-06-18 2000-09-26 Resmed Limited Facial masks for assisted respiration or CPAP
US6152129A (en) 1996-08-14 2000-11-28 Resmed Limited Determination of leak and respiratory airflow
US6182657B1 (en) 1995-09-18 2001-02-06 Resmed Limited Pressure control in CPAP treatment or assisted respiration
US6213119B1 (en) 1995-10-23 2001-04-10 Resmed Limited Inspiratory duration in CPAP or assisted respiration treatment
US6223744B1 (en) 1999-03-16 2001-05-01 Multi-Vet Ltd. Wearable aerosol delivery apparatus
US6237592B1 (en) 1995-07-03 2001-05-29 Resmed Limited Auto-calibration of pressure transducer offset
US6237593B1 (en) 1993-12-03 2001-05-29 Resmed Limited Estimation of flow and detection of breathing CPAP treatment
US6240921B1 (en) 1993-12-01 2001-06-05 Resmed, Ltd. Automated stop/start control in the administration of CPAP treatment
US6318360B1 (en) * 1998-09-10 2001-11-20 Medel S.P.A. Single-unit apparatus for aerosol therapy with integrated compressor group and associated method of assembly
US6332463B1 (en) 1995-09-15 2001-12-25 Resmed Limited Flow estimation and compensation of flow-induced pressure swings in CPAP treatment and assisted respiration
US6336454B1 (en) 1997-05-16 2002-01-08 Resmed Limited Nasal ventilation as a treatment for stroke
US6363932B1 (en) 2000-07-06 2002-04-02 Clinical Technologies, Inc. Aerosol enhancement device
US6367474B1 (en) * 1997-11-07 2002-04-09 Resmed Limited Administration of CPAP treatment pressure in presence of APNEA
US6397841B1 (en) 1997-06-18 2002-06-04 Resmed Limited Apparatus for supplying breathable gas
US6412481B1 (en) * 1999-12-23 2002-07-02 Robert Bienvenu Sealed backpressure attachment device for nebulizer
US20020121275A1 (en) * 2000-07-06 2002-09-05 Clinical Technologies, Inc. Aerosol enhancement device
US6450163B1 (en) 1997-08-29 2002-09-17 Trudell Medical International Breath actuated nebulizer with valve assembly having a relief piston
US20020157663A1 (en) * 2001-03-20 2002-10-31 Rick Blacker Nebulizer apparatus and method
US6494207B1 (en) 1996-12-02 2002-12-17 Resmed Limited Harness assembly for a nasal mask
US6510846B1 (en) * 1999-12-23 2003-01-28 O'rourke Sam Sealed back pressure breathing device
US6513526B2 (en) 1996-07-26 2003-02-04 Resmed Limited Full-face mask and mask cushion therefor
US6532957B2 (en) 1996-09-23 2003-03-18 Resmed Limited Assisted ventilation to match patient respiratory need
US6561190B1 (en) 1997-02-10 2003-05-13 Resmed Limited Mask and a vent assembly therefor
US6561191B1 (en) 1997-02-10 2003-05-13 Resmed Limited Mask and a vent assembly therefor
US20030136399A1 (en) * 2001-12-21 2003-07-24 Foley Martin P. Nebulizer apparatus and method
US6612303B1 (en) * 1996-02-13 2003-09-02 1263152 Ontario Inc. Nebulizer apparatus and method
US20030221691A1 (en) * 2000-10-19 2003-12-04 Achim Biener Breathing mask for feeding a breathing gas to a mask user and discharge device for discharging breathing gas
US6772754B1 (en) * 1999-12-30 2004-08-10 Terry Michael Mendenhall Breath actuated nebulizer controller apparatus and method
US6805118B2 (en) * 1998-03-05 2004-10-19 Zivena, Inc. Pulmonary dosing system and method
US20040206351A1 (en) * 2001-12-17 2004-10-21 Mcfarland Joseph L Portable, handheld, pneumatic driven medicinal nebulizer
USD498529S1 (en) 1996-07-26 2004-11-16 Resmed Limited Portion of a cushion for use with a mask assembly in the application of continuous positive airway pressure (CPAP)
US20050000519A1 (en) * 1999-04-07 2005-01-06 Harri Friberg Ventilator
US20050061318A1 (en) * 2003-09-22 2005-03-24 Faram Joseph Dee Continuous high-frequency oscillation breathing treatment apparatus
US20050183725A1 (en) * 2004-02-24 2005-08-25 Microdose Technologies, Inc. Directional flow sensor inhaler
US20050229929A1 (en) * 2004-04-20 2005-10-20 Aerogen, Inc. Aerosol delivery apparatus and method for pressure-assisted breathing systems
US20050235985A1 (en) * 2004-04-21 2005-10-27 Dhd Healthcare Corporation Nebulizer with auxiliary inlet port
US20060237090A1 (en) * 2003-03-11 2006-10-26 Prolitec, S.A. Method and device for nebulisation
US7267120B2 (en) 2002-08-19 2007-09-11 Allegiance Corporation Small volume nebulizer
US20070209659A1 (en) * 1995-04-05 2007-09-13 Aerogen, Inc. Liquid dispensing apparatus and methods
US7270123B2 (en) 2003-08-13 2007-09-18 Trudell Medical International Nebulizer apparatus and method
US20070256690A1 (en) * 2006-05-03 2007-11-08 Joseph Dee Faram Breathing treatment apparatus
US7401111B1 (en) 1997-12-04 2008-07-15 Roche Diagnostic Operations, Inc. Instrument setup utility program
US20080245368A1 (en) * 2007-04-02 2008-10-09 Dunsmore Thomas J High frequency oscillation respiratory therapy
US20090101144A1 (en) * 2003-12-04 2009-04-23 Gamard Stephan C F Portable gas operating inhaler
US20090188500A1 (en) * 2008-01-29 2009-07-30 Joseph Dee Faram Combination breathing treatment method
US7571722B2 (en) 2004-02-24 2009-08-11 Boehringer Ingelheim International Gmbh Nebulizer
US20090241960A1 (en) * 2008-04-01 2009-10-01 Event Medical, Inc. Dual high and low pressure breathing system
US7600511B2 (en) * 2001-11-01 2009-10-13 Novartis Pharma Ag Apparatus and methods for delivery of medicament to a respiratory system
US7654263B2 (en) 2002-01-17 2010-02-02 Map Medizin-Technologie Gmbh Breathing mask arrangement and a forehead support device for same
US7730886B2 (en) 1993-11-05 2010-06-08 Resmed Limited Determination of patency of the airway
US7762259B2 (en) 2003-04-10 2010-07-27 Resmed Limited Mask with integral cushion and forehead piece
US7779841B2 (en) 2006-11-13 2010-08-24 Carefusion 2200, Inc. Respiratory therapy device and method
US7926487B2 (en) 2000-05-15 2011-04-19 Resmed Limited Respiratory mask having gas washout vent and gas washout vent assembly for a respiratory mask
US7931023B2 (en) 1991-12-20 2011-04-26 Resmed Limited Patient interface assembly for CPAP respiratory apparatus
US7942149B2 (en) 1999-03-29 2011-05-17 Resmed Limited Forehead support for a facial mask
US7942150B2 (en) 2004-04-09 2011-05-17 Resmed Limited Nasal assembly
US7967014B2 (en) 2001-10-22 2011-06-28 Map Medizin-Technologie Gmbh Application device for breathing mask arrangement
US7971588B2 (en) 2000-05-05 2011-07-05 Novartis Ag Methods and systems for operating an aerosol generator
US7992559B2 (en) 2001-10-22 2011-08-09 Map Medizin-Technologie Gmbh Breathing mask arrangement as well as an application device and a forehead support device for same
US8028698B2 (en) 2006-09-18 2011-10-04 Invacare Corporation Breathing mask
US8051854B2 (en) 2006-09-15 2011-11-08 Comedica Incorporated Continuous high-frequency oscillation breathing treatment apparatus
US8074642B2 (en) 2002-05-21 2011-12-13 Trudell Medical International Visual indicator for an aerosol medication delivery apparatus and system
US8146592B2 (en) 2004-02-26 2012-04-03 Ameriflo, Inc. Method and apparatus for regulating fluid flow or conserving fluid flow
US8186348B2 (en) 1999-06-18 2012-05-29 Resmed Limited Forehead support for facial mask
US8230859B1 (en) 2004-02-26 2012-07-31 Ameriflo, Inc. Method and apparatus for regulating fluid
US8251876B2 (en) 2008-04-22 2012-08-28 Hill-Rom Services, Inc. Breathing exercise apparatus
US8332020B2 (en) 2010-02-01 2012-12-11 Proteus Digital Health, Inc. Two-wrist data gathering system
US8336545B2 (en) 2000-05-05 2012-12-25 Novartis Pharma Ag Methods and systems for operating an aerosol generator
US8353294B2 (en) 2004-06-16 2013-01-15 Resmed Limited Respiratory mask assembly
US8419638B2 (en) 2007-11-19 2013-04-16 Proteus Digital Health, Inc. Body-associated fluid transport structure evaluation devices
US8459252B2 (en) 2002-05-02 2013-06-11 Pari Innovative Manufacturers, Inc. Aerosol medication inhalation system
US8460223B2 (en) 2006-03-15 2013-06-11 Hill-Rom Services Pte. Ltd. High frequency chest wall oscillation system
US8485179B1 (en) 2009-02-23 2013-07-16 Trudell Medical International Oscillating positive expiratory pressure device
US8485192B2 (en) 2005-01-12 2013-07-16 Resmed Limited Cushion for patient interface
US8505535B2 (en) 2003-05-02 2013-08-13 Resmed Limited Mask system
US8517023B2 (en) 2007-01-30 2013-08-27 Resmed Limited Mask system with interchangeable headgear connectors
US8522784B2 (en) 2008-03-04 2013-09-03 Resmed Limited Mask system
US8522785B2 (en) 2002-08-05 2013-09-03 Resmed Limited Inextensible headgear and CPAP or ventilator mask assembly with the same
US8539951B1 (en) 2008-05-27 2013-09-24 Trudell Medical International Oscillating positive respiratory pressure device
USRE45068E1 (en) 2000-04-11 2014-08-12 Trudell Medical International Aerosol delivery apparatus
US8844537B1 (en) 2010-10-13 2014-09-30 Michael T. Abramson System and method for alleviating sleep apnea
US8869797B2 (en) 2007-04-19 2014-10-28 Resmed Limited Cushion and cushion to frame assembly mechanism for patient interface
US8944061B2 (en) 2005-10-14 2015-02-03 Resmed Limited Cushion to frame assembly mechanism
US8985111B2 (en) 2008-10-28 2015-03-24 Trudell Medical International Oscillating positive expiratory pressure device
US9014779B2 (en) 2010-02-01 2015-04-21 Proteus Digital Health, Inc. Data gathering system
USD731050S1 (en) 2011-06-06 2015-06-02 Trudell Medical International Oscillating positive expiratory pressure device
US9050434B2 (en) 2007-05-18 2015-06-09 Comedica Incorporated Lung therapy device
US9072853B2 (en) 2001-09-07 2015-07-07 Resmed Limited Forehead pad for respiratory mask
US9084566B2 (en) 2006-07-07 2015-07-21 Proteus Digital Health, Inc. Smart parenteral administration system
US9125979B2 (en) 2007-10-25 2015-09-08 Proteus Digital Health, Inc. Fluid transfer port information system
US9149589B2 (en) 2009-02-23 2015-10-06 Trudell Medical International Method and device for performing orientation dependent oscillating positive expiratory pressure therapy
US9151425B2 (en) 2009-11-02 2015-10-06 Comedica Incorporated Multiple conduit connector apparatus and method
US9180271B2 (en) 2012-03-05 2015-11-10 Hill-Rom Services Pte. Ltd. Respiratory therapy device having standard and oscillatory PEP with nebulizer
US9381316B2 (en) 2005-10-25 2016-07-05 Resmed Limited Interchangeable mask assembly
US9511202B1 (en) * 2012-12-04 2016-12-06 Mercury Enterprises, Inc. Breathing assistance device with nebulizer
US9517315B2 (en) 2012-11-30 2016-12-13 Trudell Medical International Oscillating positive expiratory pressure device
USD778429S1 (en) 2015-09-02 2017-02-07 Trudell Medical International Respiratory treatment device
USD780906S1 (en) 2015-09-02 2017-03-07 Trudell Medical International Respiratory treatment device
US9795752B2 (en) 2012-12-03 2017-10-24 Mhs Care-Innovation, Llc Combination respiratory therapy device, system, and method
US9802021B2 (en) 2002-12-06 2017-10-31 Fisher & Paykel Healthcare Limited Mouthpiece
US9849257B2 (en) 2013-08-22 2017-12-26 Trudell Medical International Oscillating positive respiratory pressure device

Families Citing this family (47)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB2345010B (en) * 1998-12-17 2002-12-31 Electrosols Ltd A delivery device
US6530370B1 (en) * 1999-09-16 2003-03-11 Instrumentation Corp. Nebulizer apparatus
US6964647B1 (en) * 2000-10-06 2005-11-15 Ellaz Babaev Nozzle for ultrasound wound treatment
US6769626B1 (en) 2000-10-30 2004-08-03 Instrumentarium Corp. Device and method for detecting and controlling liquid supply to an apparatus discharging liquids
US6601581B1 (en) 2000-11-01 2003-08-05 Advanced Medical Applications, Inc. Method and device for ultrasound drug delivery
US6533803B2 (en) 2000-12-22 2003-03-18 Advanced Medical Applications, Inc. Wound treatment method and device with combination of ultrasound and laser energy
US6761729B2 (en) 2000-12-22 2004-07-13 Advanced Medicalapplications, Inc. Wound treatment method and device with combination of ultrasound and laser energy
US8235919B2 (en) 2001-01-12 2012-08-07 Celleration, Inc. Ultrasonic method and device for wound treatment
US7914470B2 (en) 2001-01-12 2011-03-29 Celleration, Inc. Ultrasonic method and device for wound treatment
US6960173B2 (en) * 2001-01-30 2005-11-01 Eilaz Babaev Ultrasound wound treatment method and device using standing waves
US6623444B2 (en) 2001-03-21 2003-09-23 Advanced Medical Applications, Inc. Ultrasonic catheter drug delivery method and device
US6478754B1 (en) 2001-04-23 2002-11-12 Advanced Medical Applications, Inc. Ultrasonic method and device for wound treatment
GB0115355D0 (en) * 2001-06-22 2001-08-15 Pirrie Alastair Vaporization system
US6705316B2 (en) 2002-03-11 2004-03-16 Battelle Pulmonary Therapeutics, Inc. Pulmonary dosing system and method
JP4243499B2 (en) * 2002-06-11 2009-03-25 富士通株式会社 Bonded substrate manufacturing apparatus and the bonded substrate manufacturing method pasting
US20040094149A1 (en) * 2002-11-14 2004-05-20 Creative Biomedics, Inc. Pulmonary function filter, pulmonary sensor combination and components thereof
US7588033B2 (en) 2003-06-18 2009-09-15 Breathe Technologies, Inc. Methods, systems and devices for improving ventilation in a lung area
US8381729B2 (en) 2003-06-18 2013-02-26 Breathe Technologies, Inc. Methods and devices for minimally invasive respiratory support
CA2536090C (en) 2003-08-18 2014-07-22 Anthony D. Wondka Method and device for non-invasive ventilation with nasal interface
US7785277B2 (en) * 2005-06-23 2010-08-31 Celleration, Inc. Removable applicator nozzle for ultrasound wound therapy device
US7713218B2 (en) 2005-06-23 2010-05-11 Celleration, Inc. Removable applicator nozzle for ultrasound wound therapy device
JP2009508645A (en) 2005-09-20 2009-03-05 グレゴリー カプスト, System for assisting the breathing of the patient, methods, and apparatus
WO2007142812A3 (en) 2006-05-18 2008-10-16 Breathe Technologies Inc Tracheotomy method and device
US8562547B2 (en) 2006-06-07 2013-10-22 Eliaz Babaev Method for debriding wounds
US7431704B2 (en) * 2006-06-07 2008-10-07 Bacoustics, Llc Apparatus and method for the treatment of tissue with ultrasound energy by direct contact
WO2008079379A1 (en) * 2006-12-22 2008-07-03 Celleration, Inc. Apparatus to prevent applicator re-use
US8491521B2 (en) 2007-01-04 2013-07-23 Celleration, Inc. Removable multi-channel applicator nozzle
WO2008085911A1 (en) * 2007-01-04 2008-07-17 Celleration, Inc. Removable multi-channel applicator nozzle
JP5519510B2 (en) 2007-09-26 2014-06-11 ブリーズ・テクノロジーズ・インコーポレーテッド Ventilation equipment
CN101888868B (en) 2007-09-26 2014-01-22 呼吸科技公司 Methods and devices for treating sleep apnea
EP2231279A1 (en) * 2007-12-28 2010-09-29 Celleration, Inc. Methods for treating inflammatory skin disorders
EP2274036A4 (en) 2008-04-18 2014-08-13 Breathe Technologies Inc Methods and devices for sensing respiration and controlling ventilator functions
US8776793B2 (en) 2008-04-18 2014-07-15 Breathe Technologies, Inc. Methods and devices for sensing respiration and controlling ventilator functions
EP2326376A4 (en) 2008-08-22 2014-10-01 Breathe Technologies Inc Methods and devices for providing mechanical ventilation with an open airway interface
US8302602B2 (en) 2008-09-30 2012-11-06 Nellcor Puritan Bennett Llc Breathing assistance system with multiple pressure sensors
US9132250B2 (en) 2009-09-03 2015-09-15 Breathe Technologies, Inc. Methods, systems and devices for non-invasive ventilation including a non-sealing ventilation interface with an entrainment port and/or pressure feature
US20130255683A2 (en) 2009-04-02 2013-10-03 Breathe Technologies, Inc. Methods, Systems and Devices for Non-Invasive Open Ventilation For Providing Ventilation Support
US9962512B2 (en) 2009-04-02 2018-05-08 Breathe Technologies, Inc. Methods, systems and devices for non-invasive ventilation including a non-sealing ventilation interface with a free space nozzle feature
US20110100360A1 (en) * 2009-11-02 2011-05-05 Joseph Dee Faram Composite lung therapy device and method
US8944050B2 (en) * 2010-08-13 2015-02-03 The Corporation Of Mercer University Inhalation airflow regulation devices and methods of using the same
JP6297329B2 (en) 2010-09-30 2018-03-20 ブリーズ・テクノロジーズ・インコーポレーテッド Nose interface device
US9364624B2 (en) 2011-12-07 2016-06-14 Covidien Lp Methods and systems for adaptive base flow
US9498589B2 (en) 2011-12-31 2016-11-22 Covidien Lp Methods and systems for adaptive base flow and leak compensation
US8844526B2 (en) 2012-03-30 2014-09-30 Covidien Lp Methods and systems for triggering with unknown base flow
US9808591B2 (en) 2014-08-15 2017-11-07 Covidien Lp Methods and systems for breath delivery synchronization
US9950129B2 (en) 2014-10-27 2018-04-24 Covidien Lp Ventilation triggering using change-point detection
US9925346B2 (en) 2015-01-20 2018-03-27 Covidien Lp Systems and methods for ventilation with unknown exhalation flow

Citations (22)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US515504A (en) * 1894-02-27 Atomizer
US533489A (en) * 1895-02-05 Thomas edwin ogram
US3301255A (en) * 1963-10-18 1967-01-31 Harris A Thompson Method and apparatus for application of nebulized medication in positive pressure respiratory equipment
US3598116A (en) * 1969-06-17 1971-08-10 United Aircraft Corp Respirator with fluid amplifiers
US3664337A (en) * 1970-04-15 1972-05-23 Bio Logics Inc Respiration assembly and methods
US3826255A (en) * 1972-06-22 1974-07-30 Hudson Oxygen Therapy Sales Co Intermittent positive pressure breathing manifold
US3831596A (en) * 1971-11-10 1974-08-27 Synthelabo Control device for a respiratory apparatus
US4036253A (en) * 1975-11-12 1977-07-19 Peace Medical Gas dilution device
US4106503A (en) * 1977-03-11 1978-08-15 Richard R. Rosenthal Metering system for stimulating bronchial spasm
US4278110A (en) * 1979-11-13 1981-07-14 Price Ernest H Demand responsive flow controller
US4357936A (en) * 1979-03-05 1982-11-09 Bear Medical Systems, Inc. Directional thermistor assist sensing
US4381002A (en) * 1980-12-18 1983-04-26 The United States Of America As Represented By The Secretary Of The Army Fluidic-controlled oxygen intermittent demand flow device
US4396015A (en) * 1980-12-22 1983-08-02 Johnson Robert J Medication control device for use in treating lungs
US4446863A (en) * 1982-04-16 1984-05-08 Howard Rubin Connector for inhalation therapy apparatus
US4457303A (en) * 1980-11-26 1984-07-03 Tritec Industries, Inc. Respirating gas supply control method and apparatus therefor
US4637384A (en) * 1985-02-15 1987-01-20 The Boc Group, Inc. Coaxial breathing circuit
US4677975A (en) * 1984-10-16 1987-07-07 The University Of Auckland Method of dispensing and/or a dispenser
US4832012A (en) * 1987-07-08 1989-05-23 Vortran Medical Technology, Inc. Intermittent signal actuated nebulizer
US4848333A (en) * 1986-12-09 1989-07-18 Waite & Co. Pty. Limited Oxygen dilution apparatus
US5080093A (en) * 1987-07-08 1992-01-14 Vortran Medical Technology, Inc. Intermittant signal actuated nebulizer
US5099837A (en) * 1990-09-28 1992-03-31 Russel Sr Larry L Inhalation-based control of medical gas
US5193532A (en) * 1988-12-06 1993-03-16 Moa Conny P G Device for generating by means of ejector action a continuous positive airway pressure (cpap) during spontaneous breathing

Family Cites Families (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US724675A (en) * 1902-08-29 1903-04-07 William M Ferry Fluid-conducting pipe.
US2280140A (en) * 1939-11-28 1942-04-21 Wilson John Hart Fuel supply means for power plants
US3291508A (en) * 1964-12-21 1966-12-13 Int Harvester Co Flexible fluid joint
US3885820A (en) * 1973-11-05 1975-05-27 Dow Chemical Co Tubing connector
US5570682A (en) * 1993-12-14 1996-11-05 Ethex International, Inc. Passive inspiratory nebulizer system

Patent Citations (22)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US533489A (en) * 1895-02-05 Thomas edwin ogram
US515504A (en) * 1894-02-27 Atomizer
US3301255A (en) * 1963-10-18 1967-01-31 Harris A Thompson Method and apparatus for application of nebulized medication in positive pressure respiratory equipment
US3598116A (en) * 1969-06-17 1971-08-10 United Aircraft Corp Respirator with fluid amplifiers
US3664337A (en) * 1970-04-15 1972-05-23 Bio Logics Inc Respiration assembly and methods
US3831596A (en) * 1971-11-10 1974-08-27 Synthelabo Control device for a respiratory apparatus
US3826255A (en) * 1972-06-22 1974-07-30 Hudson Oxygen Therapy Sales Co Intermittent positive pressure breathing manifold
US4036253A (en) * 1975-11-12 1977-07-19 Peace Medical Gas dilution device
US4106503A (en) * 1977-03-11 1978-08-15 Richard R. Rosenthal Metering system for stimulating bronchial spasm
US4357936A (en) * 1979-03-05 1982-11-09 Bear Medical Systems, Inc. Directional thermistor assist sensing
US4278110A (en) * 1979-11-13 1981-07-14 Price Ernest H Demand responsive flow controller
US4457303A (en) * 1980-11-26 1984-07-03 Tritec Industries, Inc. Respirating gas supply control method and apparatus therefor
US4381002A (en) * 1980-12-18 1983-04-26 The United States Of America As Represented By The Secretary Of The Army Fluidic-controlled oxygen intermittent demand flow device
US4396015A (en) * 1980-12-22 1983-08-02 Johnson Robert J Medication control device for use in treating lungs
US4446863A (en) * 1982-04-16 1984-05-08 Howard Rubin Connector for inhalation therapy apparatus
US4677975A (en) * 1984-10-16 1987-07-07 The University Of Auckland Method of dispensing and/or a dispenser
US4637384A (en) * 1985-02-15 1987-01-20 The Boc Group, Inc. Coaxial breathing circuit
US4848333A (en) * 1986-12-09 1989-07-18 Waite & Co. Pty. Limited Oxygen dilution apparatus
US4832012A (en) * 1987-07-08 1989-05-23 Vortran Medical Technology, Inc. Intermittent signal actuated nebulizer
US5080093A (en) * 1987-07-08 1992-01-14 Vortran Medical Technology, Inc. Intermittant signal actuated nebulizer
US5193532A (en) * 1988-12-06 1993-03-16 Moa Conny P G Device for generating by means of ejector action a continuous positive airway pressure (cpap) during spontaneous breathing
US5099837A (en) * 1990-09-28 1992-03-31 Russel Sr Larry L Inhalation-based control of medical gas

Non-Patent Citations (4)

* Cited by examiner, † Cited by third party
Title
Auerbach et al, A New Oxygen Cannula System using Intermittent Demand Nasal Flow, Chest, 74:1, Jul. 1978, pp. 39 44. *
Auerbach et al, A New Oxygen Cannula System using Intermittent-Demand Nasal Flow, Chest, 74:1, Jul. 1978, pp. 39-44.
Mon, The Design of a Fluidic Oxygen Intermittent Demand Flow Device, Report No. HDL TM 80 14, Harry Diamond Laboratories, Adelphi, MD. 20783, Mar. 1980, pp. 5 8. *
Mon, The Design of a Fluidic Oxygen Intermittent-Demand Flow Device, Report No. HDL-TM-80-14, Harry Diamond Laboratories, Adelphi, MD. 20783, Mar. 1980, pp. 5-8.

Cited By (275)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7931023B2 (en) 1991-12-20 2011-04-26 Resmed Limited Patient interface assembly for CPAP respiratory apparatus
US6123071A (en) 1993-06-18 2000-09-26 Resmed Limited Facial masks for assisted respiration or CPAP
US8752547B2 (en) 1993-11-05 2014-06-17 Resmed Limited Distinguishing between closed and open airway apneas and treating patients accordingly
US8381722B2 (en) 1993-11-05 2013-02-26 Resmed Limited Distinguishing between closed and open airway apneas and treating patients accordingly
US8360060B2 (en) 1993-11-05 2013-01-29 Resmed Limited Distinguishing between closed and open airway apneas and treating patients accordingly
US6138675A (en) 1993-11-05 2000-10-31 Resmed Ltd. Determination of the occurrence of an apnea
US6029665A (en) 1993-11-05 2000-02-29 Resmed Limited Determination of patency of airway
US7730886B2 (en) 1993-11-05 2010-06-08 Resmed Limited Determination of patency of the airway
US6240921B1 (en) 1993-12-01 2001-06-05 Resmed, Ltd. Automated stop/start control in the administration of CPAP treatment
US6237593B1 (en) 1993-12-03 2001-05-29 Resmed Limited Estimation of flow and detection of breathing CPAP treatment
US6076519A (en) * 1993-12-14 2000-06-20 Ethex International, Inc. Passive inspiratory nebulizer system
US8561604B2 (en) * 1995-04-05 2013-10-22 Novartis Ag Liquid dispensing apparatus and methods
US20070209659A1 (en) * 1995-04-05 2007-09-13 Aerogen, Inc. Liquid dispensing apparatus and methods
US6363270B1 (en) 1995-04-11 2002-03-26 Resmed Limited Monitoring the occurrence of apneic and hypopneic arousals
US6091973A (en) 1995-04-11 2000-07-18 Resmed Limited Monitoring the occurrence of apneic and hypopneic arousals
US6237592B1 (en) 1995-07-03 2001-05-29 Resmed Limited Auto-calibration of pressure transducer offset
US6332463B1 (en) 1995-09-15 2001-12-25 Resmed Limited Flow estimation and compensation of flow-induced pressure swings in CPAP treatment and assisted respiration
US6182657B1 (en) 1995-09-18 2001-02-06 Resmed Limited Pressure control in CPAP treatment or assisted respiration
US6526974B1 (en) 1995-09-18 2003-03-04 John William Ernest Brydon Pressure control in CPAP treatment or assisted respiration
US6213119B1 (en) 1995-10-23 2001-04-10 Resmed Limited Inspiratory duration in CPAP or assisted respiration treatment
US5699786A (en) * 1995-10-31 1997-12-23 Sanyo Electric Co., Ltd. Atomizer system
US7080643B2 (en) 1996-02-13 2006-07-25 Trudell Medical Internationl Nebulizer apparatus and method
US7634995B2 (en) 1996-02-13 2009-12-22 Trudell Medical International Nebulizer apparatus and method
US6644304B2 (en) 1996-02-13 2003-11-11 1263152 Ontario Inc. Nebulizer apparatus and method
US6748945B2 (en) 1996-02-13 2004-06-15 Trudell Medical International Nebulizer apparatus and method
US20040173209A1 (en) * 1996-02-13 2004-09-09 Trudell Medical International. Nebulizer apparatus and method
US6612303B1 (en) * 1996-02-13 2003-09-02 1263152 Ontario Inc. Nebulizer apparatus and method
US8061352B2 (en) 1996-02-13 2011-11-22 Trudell Medical International Aerosol delivery apparatus and method
US6581602B2 (en) 1996-07-26 2003-06-24 Resmed Limited Nasal mask and mask cushion therefor
US7950392B2 (en) 1996-07-26 2011-05-31 Resmed Limited Cushion and mask therefor
US8813748B2 (en) 1996-07-26 2014-08-26 Resmed Limited Full-face mask and mask cushion therefor
US9421339B2 (en) 1996-07-26 2016-08-23 Resmed Limited Patient interface
US6112746A (en) 1996-07-26 2000-09-05 Resmed Limited Nasal mask and mask cushion therefor
US6513526B2 (en) 1996-07-26 2003-02-04 Resmed Limited Full-face mask and mask cushion therefor
US8056561B2 (en) 1996-07-26 2011-11-15 Resmed Limited Full-face mask and mask cushion therefor
US6357441B1 (en) 1996-07-26 2002-03-19 Resmed Limited Nasal mask and mask cushion therefor
US8636006B2 (en) 1996-07-26 2014-01-28 Resmed Limited Mask
US9463295B2 (en) 1996-07-26 2016-10-11 Resmed Limited Mask and mask cushion therefor
US8522783B2 (en) 1996-07-26 2013-09-03 Resmed Limited Cushion and mask therefor
US6701927B2 (en) 1996-07-26 2004-03-09 Resmed Limited Full-face mask and mask cushion therefor
US6634358B2 (en) 1996-07-26 2003-10-21 Resmed Limited Nasal mask cushion assembly
USD498529S1 (en) 1996-07-26 2004-11-16 Resmed Limited Portion of a cushion for use with a mask assembly in the application of continuous positive airway pressure (CPAP)
US6279569B1 (en) 1996-08-14 2001-08-28 Resmed Limited Determination of leak and respiratory airflow
US6152129A (en) 1996-08-14 2000-11-28 Resmed Limited Determination of leak and respiratory airflow
US6688307B2 (en) 1996-09-23 2004-02-10 Resmed Limited Methods and apparatus for determining instantaneous elastic recoil and assistance pressure during ventilatory support
US9974911B2 (en) 1996-09-23 2018-05-22 Resmed Limited Method and apparatus for providing ventilatory assistance
US7644713B2 (en) 1996-09-23 2010-01-12 Resmed Limited Method and apparatus for determining instantaneous leak during ventilatory assistance
US8733351B2 (en) 1996-09-23 2014-05-27 Resmed Limited Method and apparatus for providing ventilatory assistance
US8051853B2 (en) 1996-09-23 2011-11-08 Resmed Limited Method and apparatus for providing ventilatory assistance
US6532957B2 (en) 1996-09-23 2003-03-18 Resmed Limited Assisted ventilation to match patient respiratory need
US6810876B2 (en) 1996-09-23 2004-11-02 Resmed Ltd. Assisted ventilation to match patient respiratory need
US6006748A (en) 1996-10-16 1999-12-28 Resmed Limited Vent valve apparatus
US8997739B2 (en) 1996-10-16 2015-04-07 Resmed Limited Vent valve apparatus
US6494207B1 (en) 1996-12-02 2002-12-17 Resmed Limited Harness assembly for a nasal mask
US6044844A (en) 1996-12-02 2000-04-04 Resmed Limited Mask and harness assembly
US20100282251A1 (en) * 1996-12-12 2010-11-11 Resmed Limited Method and apparatus for substance delivery in system for supplying breathable gas
US6029660A (en) 1996-12-12 2000-02-29 Resmed Limited Substance delivery apparatus
US6990977B1 (en) 1996-12-12 2006-01-31 Resmed Limited Substance delivery apparatus
WO1998025662A1 (en) * 1996-12-12 1998-06-18 Resmed Limited Substance delivery in breathable gas supply system
US7779834B2 (en) 1996-12-12 2010-08-24 Resmed Limited Method and apparatus for substance delivery in system for supplying breathable gas
US8397716B2 (en) 1996-12-12 2013-03-19 Resmed Limited Method and apparatus for substance delivery in system for supplying breathable gas
GB2321419B (en) * 1997-01-27 2001-02-07 Medic Aid Ltd Atomizer
EP0855224A3 (en) * 1997-01-27 1999-07-07 Medic-Aid Limited Atomizer
US6129080A (en) * 1997-01-27 2000-10-10 Medic-Aid Limited Atomizer
US6561190B1 (en) 1997-02-10 2003-05-13 Resmed Limited Mask and a vent assembly therefor
US7845354B2 (en) 1997-02-10 2010-12-07 Resmed Limited Mask and vent assembly therefor
US8826910B2 (en) 1997-02-10 2014-09-09 Resmed Limited Mask and vent assembly therefor
US8122886B2 (en) 1997-02-10 2012-02-28 Resmed Limited Respiratory mask assembly with vent
US8833371B2 (en) 1997-02-10 2014-09-16 Resmed Limited Mask and vent assembly therefor
US6561191B1 (en) 1997-02-10 2003-05-13 Resmed Limited Mask and a vent assembly therefor
US6119723A (en) 1997-02-14 2000-09-19 Resmed Limited, Apparatus for varying the flow area of a conduit
USD428987S (en) 1997-02-25 2000-08-01 Resmed Limited Nasal mask shell
USD435650S (en) 1997-02-25 2000-12-26 Resmed Limited Combined nasal mask shell and cushion
USD423096S (en) 1997-02-25 2000-04-18 Resmed Limited Nasal mask cushion
US6076520A (en) * 1997-05-12 2000-06-20 Cooper; Emily L. Device for nasal therapeutic inhalation
US6336454B1 (en) 1997-05-16 2002-01-08 Resmed Limited Nasal ventilation as a treatment for stroke
US6776155B2 (en) 1997-05-16 2004-08-17 Resmed Limited Nasal ventilation as a treatment for stroke
US6397841B1 (en) 1997-06-18 2002-06-04 Resmed Limited Apparatus for supplying breathable gas
US6450163B1 (en) 1997-08-29 2002-09-17 Trudell Medical International Breath actuated nebulizer with valve assembly having a relief piston
US6367474B1 (en) * 1997-11-07 2002-04-09 Resmed Limited Administration of CPAP treatment pressure in presence of APNEA
US6988498B2 (en) 1997-11-07 2006-01-24 Resmed Limited Administration of CPAP treatment pressure in presence of apnea
US8511307B2 (en) 1997-11-07 2013-08-20 ResMed Limted Administration of CPAP treatment pressure in presence of apnea
US20060021618A1 (en) * 1997-11-07 2006-02-02 Michael Berthon-Jones Administration of CPAP treatment pressure in presence of apnea
US20050076910A1 (en) * 1997-11-07 2005-04-14 Michael Berthon-Jones Administration of CPAP treatment pressure in presence of apnea
US8220457B2 (en) 1997-11-07 2012-07-17 Resmed Limited Administration of CPAP treatment pressure in presence of apnea
US8684000B2 (en) 1997-11-07 2014-04-01 Resmed Limited Administration of CPAP treatment pressure in presence of apnea
US9526855B2 (en) 1997-11-07 2016-12-27 Resmed Limited Administration of CPAP treatment pressure in presence of apnea
US20090038617A1 (en) * 1997-11-07 2009-02-12 Michael Berthon-Jones Administration of cpap treatment in presence of apnea
US6105929A (en) * 1997-11-14 2000-08-22 Salter Labs Control valve for gas supply to a nebulizer
WO1999026004A1 (en) 1997-11-14 1999-05-27 Salter Labs Pilot valve
US7401111B1 (en) 1997-12-04 2008-07-15 Roche Diagnostic Operations, Inc. Instrument setup utility program
US6119693A (en) 1998-01-16 2000-09-19 Resmed Limited Forehead support for facial mask
US7882837B2 (en) 1998-01-16 2011-02-08 Resmed Limited Forehead support for facial mask
US9220861B2 (en) 1998-01-16 2015-12-29 Resmed Limited Forehead support for facial mask
USD782028S1 (en) 1998-01-16 2017-03-21 Resmed Limited Pad for forehead support
US6463931B1 (en) 1998-01-16 2002-10-15 Resmed Limited Forehead support for facial mask
US6691708B2 (en) 1998-01-16 2004-02-17 Resmed Limited Forehead support for facial mask
USD807497S1 (en) 1998-01-16 2018-01-09 Resmed Limited Pad for forehead support
US6557556B2 (en) 1998-01-16 2003-05-06 Resmed Limited Forehead support for facial mask
US6805118B2 (en) * 1998-03-05 2004-10-19 Zivena, Inc. Pulmonary dosing system and method
USD421298S (en) 1998-04-23 2000-02-29 Resmed Limited Flow generator
US6041776A (en) * 1998-05-14 2000-03-28 Briggs, Iii; Stephen W. Medical nebulization device
USRE38700E1 (en) * 1998-05-14 2005-02-15 Briggs Iii Stephen W Medical nebulization device
US6318360B1 (en) * 1998-09-10 2001-11-20 Medel S.P.A. Single-unit apparatus for aerosol therapy with integrated compressor group and associated method of assembly
US6223744B1 (en) 1999-03-16 2001-05-01 Multi-Vet Ltd. Wearable aerosol delivery apparatus
US7942149B2 (en) 1999-03-29 2011-05-17 Resmed Limited Forehead support for a facial mask
US8646450B2 (en) 1999-03-29 2014-02-11 Resmed Limited Forehead support for a facial mask
US7219666B2 (en) 1999-04-07 2007-05-22 Event Medical Limited Ventilator
US20050000519A1 (en) * 1999-04-07 2005-01-06 Harri Friberg Ventilator
US8186348B2 (en) 1999-06-18 2012-05-29 Resmed Limited Forehead support for facial mask
US9592359B2 (en) 1999-06-18 2017-03-14 Resmed Limited Forehead support for facial mask
US6510846B1 (en) * 1999-12-23 2003-01-28 O'rourke Sam Sealed back pressure breathing device
US6609515B2 (en) 1999-12-23 2003-08-26 Robert Bienvenu Sealed backpressure attachment device for nebulizer
US6412481B1 (en) * 1999-12-23 2002-07-02 Robert Bienvenu Sealed backpressure attachment device for nebulizer
US6772754B1 (en) * 1999-12-30 2004-08-10 Terry Michael Mendenhall Breath actuated nebulizer controller apparatus and method
USRE45068E1 (en) 2000-04-11 2014-08-12 Trudell Medical International Aerosol delivery apparatus
USRE46050E1 (en) 2000-04-11 2016-07-05 Trudell Medical International Aerosol delivery apparatus
US7971588B2 (en) 2000-05-05 2011-07-05 Novartis Ag Methods and systems for operating an aerosol generator
US8336545B2 (en) 2000-05-05 2012-12-25 Novartis Pharma Ag Methods and systems for operating an aerosol generator
US8528558B2 (en) 2000-05-15 2013-09-10 Resmed Limited Respiratory mask having washout vent and gas washout vent assembly for a respiratory mask
US7926487B2 (en) 2000-05-15 2011-04-19 Resmed Limited Respiratory mask having gas washout vent and gas washout vent assembly for a respiratory mask
US7204245B2 (en) 2000-07-06 2007-04-17 Clinical Technologies, Inc Aerosol enhancement device
US20070169774A1 (en) * 2000-07-06 2007-07-26 Clinical Technologies, Inc. Aerosol enhancement device
US6363932B1 (en) 2000-07-06 2002-04-02 Clinical Technologies, Inc. Aerosol enhancement device
US20020121275A1 (en) * 2000-07-06 2002-09-05 Clinical Technologies, Inc. Aerosol enhancement device
US20030221691A1 (en) * 2000-10-19 2003-12-04 Achim Biener Breathing mask for feeding a breathing gas to a mask user and discharge device for discharging breathing gas
US8371301B2 (en) 2000-10-19 2013-02-12 Resmed R&D Germany Gmbh Breathing mask for feeding a breathing gas to a mask user and discharge device for discharging breathing gas
US8746250B2 (en) 2000-10-19 2014-06-10 Resmed R&D Germany Gmbh Breathing mask for feeding a breathing gas to a mask user and discharge device for discharging breathing gas
US7775209B2 (en) 2000-10-19 2010-08-17 Map Medizintechnologie Gmbh Breathing mask for feeding a breathing gas to a mask user and discharge device for discharging breathing gas
US9662467B2 (en) 2000-10-19 2017-05-30 Resmed R&D Germany Gmbh Breathing mask for feeding a breathing gas to a mask user and discharge device for discharging breathing gas
US9364618B2 (en) 2001-03-20 2016-06-14 Trudell Medical International Nebulizer apparatus and method
US7905228B2 (en) 2001-03-20 2011-03-15 Trudell Medical International Nebulizer apparatus and method
US7131439B2 (en) 2001-03-20 2006-11-07 Trudell Medical International Nebulizer apparatus and method
US6929003B2 (en) 2001-03-20 2005-08-16 Trudell Medical International Nebulizer apparatus and method
US20050205085A1 (en) * 2001-03-20 2005-09-22 Trudell Medical International Nebulizer apparatus and method
US8196573B2 (en) 2001-03-20 2012-06-12 Novartis Ag Methods and systems for operating an aerosol generator
US20020157663A1 (en) * 2001-03-20 2002-10-31 Rick Blacker Nebulizer apparatus and method
US9907918B2 (en) 2001-03-20 2018-03-06 Trudell Medical International Nebulizer apparatus and method
US9072853B2 (en) 2001-09-07 2015-07-07 Resmed Limited Forehead pad for respiratory mask
US9889266B2 (en) 2001-10-22 2018-02-13 Resmed R&D Germany Gmbh Breathing mask arrangement as well as an application device and a forehead support device for same
US9144656B2 (en) 2001-10-22 2015-09-29 Resmed R&D Germany Gmbh Breathing mask arrangement as well as an application device and a forehead support device for same
US8875710B2 (en) 2001-10-22 2014-11-04 Resmed R&D Germany Gmbh Application device for a breathing mask arrangement
US9757534B2 (en) 2001-10-22 2017-09-12 Resmed R&D Germany Gmbh Breathing mask arrangement as well as an application device and a forehead support device for same
US7992559B2 (en) 2001-10-22 2011-08-09 Map Medizin-Technologie Gmbh Breathing mask arrangement as well as an application device and a forehead support device for same
US8479738B2 (en) 2001-10-22 2013-07-09 Resmed R&D Germany Gmbh Breathing mask arrangement as well as an application device and a forehead support device for same
US7967014B2 (en) 2001-10-22 2011-06-28 Map Medizin-Technologie Gmbh Application device for breathing mask arrangement
US7600511B2 (en) * 2001-11-01 2009-10-13 Novartis Pharma Ag Apparatus and methods for delivery of medicament to a respiratory system
US7013894B2 (en) * 2001-12-17 2006-03-21 Mcfarland Jr Joseph L Portable, handheld, pneumatic driven medicinal nebulizer
US20040206351A1 (en) * 2001-12-17 2004-10-21 Mcfarland Joseph L Portable, handheld, pneumatic driven medicinal nebulizer
US7568480B2 (en) 2001-12-21 2009-08-04 Trudell Medical International Nebulizer apparatus and method
US8844520B2 (en) 2001-12-21 2014-09-30 Trudell Medical International Nebulizer apparatus and method
US8397712B2 (en) 2001-12-21 2013-03-19 Trudell Medical International Nebulizer apparatus and method
US20030136399A1 (en) * 2001-12-21 2003-07-24 Foley Martin P. Nebulizer apparatus and method
US6994083B2 (en) 2001-12-21 2006-02-07 Trudell Medical International Nebulizer apparatus and method
US7559322B2 (en) 2001-12-21 2009-07-14 Trudell Medical International Nebulizer apparatus and method
US9259549B2 (en) 2002-01-17 2016-02-16 Resmed R&D Germany Gmbh Breathing mask arrangement and a forehead support device for same
US7654263B2 (en) 2002-01-17 2010-02-02 Map Medizin-Technologie Gmbh Breathing mask arrangement and a forehead support device for same
US8402972B2 (en) 2002-01-17 2013-03-26 Resmed R&D Germany Gmbh Breathing mask arrangement and a forehead support device for same
US8459252B2 (en) 2002-05-02 2013-06-11 Pari Innovative Manufacturers, Inc. Aerosol medication inhalation system
US8973571B1 (en) 2002-05-02 2015-03-10 Pre Holding, Inc. Aerosol medication inhalation system
US9308335B2 (en) 2002-05-02 2016-04-12 Pre Holding, Inc. Aerosol medication inhalation system
US8550067B2 (en) 2002-05-21 2013-10-08 Trudell Medical International Visual indicator for an aerosol medication delivery apparatus and system
US8074642B2 (en) 2002-05-21 2011-12-13 Trudell Medical International Visual indicator for an aerosol medication delivery apparatus and system
US9814849B2 (en) 2002-05-21 2017-11-14 Trudell Medical International Medication delivery apparatus and system and methods for the use and assembly thereof
US9700689B2 (en) 2002-05-21 2017-07-11 Trudell Medical International Medication delivery apparatus and system and methods for the use and assembly thereof
US9597473B2 (en) 2002-08-05 2017-03-21 Resmed Limited Inextensible headgear and CPAP or ventilator mask assembly with same
US8522785B2 (en) 2002-08-05 2013-09-03 Resmed Limited Inextensible headgear and CPAP or ventilator mask assembly with the same
US7267120B2 (en) 2002-08-19 2007-09-11 Allegiance Corporation Small volume nebulizer
US9802021B2 (en) 2002-12-06 2017-10-31 Fisher & Paykel Healthcare Limited Mouthpiece
US9956369B2 (en) 2002-12-06 2018-05-01 Fisher & Paykel Healthcare Limited Mouthpiece
US20060237090A1 (en) * 2003-03-11 2006-10-26 Prolitec, S.A. Method and device for nebulisation
US7762259B2 (en) 2003-04-10 2010-07-27 Resmed Limited Mask with integral cushion and forehead piece
US8794239B2 (en) 2003-04-10 2014-08-05 Resmed Limited Mask with integral cushion and forehead piece
US9248251B2 (en) 2003-04-10 2016-02-02 Resmed Limited Mask with integral cushion and forehead piece
US8210180B2 (en) 2003-04-10 2012-07-03 Resmed Limited Mask with integral cushion and forehead piece
US9895503B2 (en) 2003-05-02 2018-02-20 Resmed Limited Mask system
US8505535B2 (en) 2003-05-02 2013-08-13 Resmed Limited Mask system
US7270123B2 (en) 2003-08-13 2007-09-18 Trudell Medical International Nebulizer apparatus and method
US20080083407A1 (en) * 2003-08-13 2008-04-10 Trudell Medical International Nebulizer Apparatus And Method
US7954487B2 (en) 2003-08-13 2011-06-07 Trudell Medical International Nebulizer apparatus and method
US20050061318A1 (en) * 2003-09-22 2005-03-24 Faram Joseph Dee Continuous high-frequency oscillation breathing treatment apparatus
US7191780B2 (en) * 2003-09-22 2007-03-20 Comedica Incorporated Continuous high-frequency oscillation breathing treatment apparatus
US20090101144A1 (en) * 2003-12-04 2009-04-23 Gamard Stephan C F Portable gas operating inhaler
US8474452B2 (en) * 2004-02-24 2013-07-02 Microdose Therapeutx, Inc. Directional flow sensor inhaler
US7571722B2 (en) 2004-02-24 2009-08-11 Boehringer Ingelheim International Gmbh Nebulizer
US9162031B2 (en) 2004-02-24 2015-10-20 Microdose Therapeutx, Inc. Directional flow sensor inhaler
US9764104B2 (en) 2004-02-24 2017-09-19 Microdose Therapeutx, Inc. Directional flow sensor inhaler
US20050183725A1 (en) * 2004-02-24 2005-08-25 Microdose Technologies, Inc. Directional flow sensor inhaler
US8146592B2 (en) 2004-02-26 2012-04-03 Ameriflo, Inc. Method and apparatus for regulating fluid flow or conserving fluid flow
US8230859B1 (en) 2004-02-26 2012-07-31 Ameriflo, Inc. Method and apparatus for regulating fluid
US8757162B2 (en) 2004-04-09 2014-06-24 Resmed Limited Nasal assembly
US7942150B2 (en) 2004-04-09 2011-05-17 Resmed Limited Nasal assembly
US9895505B2 (en) 2004-04-09 2018-02-20 Resmed Limited Nasal assembly
US7267121B2 (en) * 2004-04-20 2007-09-11 Aerogen, Inc. Aerosol delivery apparatus and method for pressure-assisted breathing systems
US20050229929A1 (en) * 2004-04-20 2005-10-20 Aerogen, Inc. Aerosol delivery apparatus and method for pressure-assisted breathing systems
US7036500B2 (en) 2004-04-21 2006-05-02 Smiths Medical Asd, Inc. Nebulizer with auxiliary inlet port
US20050235985A1 (en) * 2004-04-21 2005-10-27 Dhd Healthcare Corporation Nebulizer with auxiliary inlet port
US8353294B2 (en) 2004-06-16 2013-01-15 Resmed Limited Respiratory mask assembly
US9375545B2 (en) 2004-06-16 2016-06-28 Resmed Limited Respiratory mask assembly
US8485192B2 (en) 2005-01-12 2013-07-16 Resmed Limited Cushion for patient interface
US9295800B2 (en) 2005-01-12 2016-03-29 Resmed Limited Cushion for patient interface
US8550083B2 (en) 2005-01-12 2013-10-08 Resmed Limited Cushion for patient interface
US8616211B2 (en) 2005-01-12 2013-12-31 Resmed Limited Cushion for patient interface
US8555885B2 (en) 2005-01-12 2013-10-15 Resmed Limited Cushion for patient interface
US8567404B2 (en) 2005-01-12 2013-10-29 Resmed Limited Cushion for patient interface
US8578935B2 (en) 2005-01-12 2013-11-12 Resmed Limited Cushion for patient interface
US8613281B2 (en) 2005-01-12 2013-12-24 Resmed Limited Cushion for patient interface
US8550081B2 (en) 2005-01-12 2013-10-08 Resmed Limited Cushion for patient interface
US8613280B2 (en) 2005-01-12 2013-12-24 Resmed Limited Cushion for patient interface
US8573213B2 (en) 2005-01-12 2013-11-05 Resmed Limited Cushion for patient interface
US8550082B2 (en) 2005-01-12 2013-10-08 Resmed Limited Cushion for patient interface
US8573215B2 (en) 2005-01-12 2013-11-05 Resmed Limited Cushion for patient interface
US8573214B2 (en) 2005-01-12 2013-11-05 Resmed Limited Cushion for patient interface
US8944061B2 (en) 2005-10-14 2015-02-03 Resmed Limited Cushion to frame assembly mechanism
US9381316B2 (en) 2005-10-25 2016-07-05 Resmed Limited Interchangeable mask assembly
US9962510B2 (en) 2005-10-25 2018-05-08 Resmed Limited Respiratory mask assembly
US9968511B2 (en) 2006-03-15 2018-05-15 Hill-Rom Services Pte. Ltd. High frequency chest wall oscillation system
US8460223B2 (en) 2006-03-15 2013-06-11 Hill-Rom Services Pte. Ltd. High frequency chest wall oscillation system
US7909033B2 (en) * 2006-05-03 2011-03-22 Comedica Incorporated Breathing treatment apparatus
US20070256690A1 (en) * 2006-05-03 2007-11-08 Joseph Dee Faram Breathing treatment apparatus
US9084566B2 (en) 2006-07-07 2015-07-21 Proteus Digital Health, Inc. Smart parenteral administration system
US8051854B2 (en) 2006-09-15 2011-11-08 Comedica Incorporated Continuous high-frequency oscillation breathing treatment apparatus
US8028698B2 (en) 2006-09-18 2011-10-04 Invacare Corporation Breathing mask
US8025054B2 (en) 2006-11-13 2011-09-27 Carefusion 2200, Inc. Passive respiratory therapy device
US8534284B2 (en) 2006-11-13 2013-09-17 Carefusion 2200, Inc. Respiratory therapy device
US20100307487A1 (en) * 2006-11-13 2010-12-09 Carefusion 2200, Inc. Respiratory therapy device and method
US7779841B2 (en) 2006-11-13 2010-08-24 Carefusion 2200, Inc. Respiratory therapy device and method
US9937315B2 (en) 2007-01-30 2018-04-10 Resmed Limited Mask with removable headgear connector
US8960196B2 (en) 2007-01-30 2015-02-24 Resmed Limited Mask system with interchangeable headgear connectors
US8517023B2 (en) 2007-01-30 2013-08-27 Resmed Limited Mask system with interchangeable headgear connectors
US8528547B2 (en) 2007-04-02 2013-09-10 Carefusion 2200, Inc. High frequency oscillation respiratory therapy
US20080245368A1 (en) * 2007-04-02 2008-10-09 Dunsmore Thomas J High frequency oscillation respiratory therapy
US8869797B2 (en) 2007-04-19 2014-10-28 Resmed Limited Cushion and cushion to frame assembly mechanism for patient interface
US9050434B2 (en) 2007-05-18 2015-06-09 Comedica Incorporated Lung therapy device
US9125979B2 (en) 2007-10-25 2015-09-08 Proteus Digital Health, Inc. Fluid transfer port information system
US8419638B2 (en) 2007-11-19 2013-04-16 Proteus Digital Health, Inc. Body-associated fluid transport structure evaluation devices
US20090188500A1 (en) * 2008-01-29 2009-07-30 Joseph Dee Faram Combination breathing treatment method
US8550084B2 (en) 2008-03-04 2013-10-08 Resmed Limited Mask system
US9119931B2 (en) 2008-03-04 2015-09-01 Resmed Limited Mask system
US8528561B2 (en) 2008-03-04 2013-09-10 Resmed Limited Mask system
US8522784B2 (en) 2008-03-04 2013-09-03 Resmed Limited Mask system
US9962511B2 (en) 2008-03-04 2018-05-08 Resmed Limited Mask system with snap-fit shroud
US9757533B2 (en) 2008-03-04 2017-09-12 Resmed Limited Mask system with snap-fit shroud
US9950131B2 (en) 2008-03-04 2018-04-24 Resmed Limited Mask system with snap-fit shroud
US9027556B2 (en) 2008-03-04 2015-05-12 Resmed Limited Mask system
US9770568B2 (en) 2008-03-04 2017-09-26 Resmed Limited Mask system with snap-fit shroud
US20090241960A1 (en) * 2008-04-01 2009-10-01 Event Medical, Inc. Dual high and low pressure breathing system
US8251876B2 (en) 2008-04-22 2012-08-28 Hill-Rom Services, Inc. Breathing exercise apparatus
US9808588B1 (en) 2008-05-27 2017-11-07 Trudell Medical International Oscillating positive respiratory pressure device
US8539951B1 (en) 2008-05-27 2013-09-24 Trudell Medical International Oscillating positive respiratory pressure device
US9636473B2 (en) 2008-05-27 2017-05-02 Trudell Medical International Oscillating positive respiratory pressure device
US9737677B2 (en) 2008-10-28 2017-08-22 Trudell Medical International Oscillating positive expiratory pressure device
US9913955B2 (en) 2008-10-28 2018-03-13 Trudell Medical International Oscillating positive expiratory pressure device
US8985111B2 (en) 2008-10-28 2015-03-24 Trudell Medical International Oscillating positive expiratory pressure device
US9220855B2 (en) 2009-02-23 2015-12-29 Trudell Medical International Oscillating positive expiratory pressure device
US8485179B1 (en) 2009-02-23 2013-07-16 Trudell Medical International Oscillating positive expiratory pressure device
US9950128B2 (en) 2009-02-23 2018-04-24 Trudell Medical International Oscillating positive expiratory pressure device
US9149589B2 (en) 2009-02-23 2015-10-06 Trudell Medical International Method and device for performing orientation dependent oscillating positive expiratory pressure therapy
US9151425B2 (en) 2009-11-02 2015-10-06 Comedica Incorporated Multiple conduit connector apparatus and method
US9014779B2 (en) 2010-02-01 2015-04-21 Proteus Digital Health, Inc. Data gathering system
US9008761B2 (en) 2010-02-01 2015-04-14 Proteus Digital Health, Inc. Two-wrist data gathering system
US8332020B2 (en) 2010-02-01 2012-12-11 Proteus Digital Health, Inc. Two-wrist data gathering system
US8844537B1 (en) 2010-10-13 2014-09-30 Michael T. Abramson System and method for alleviating sleep apnea
US9763767B2 (en) 2010-10-13 2017-09-19 Michael T. Abramson System and method for alleviating sleep apnea
USD776804S1 (en) 2011-06-06 2017-01-17 Trudell Medical International Oscillating positive expiratory pressure device
USD731050S1 (en) 2011-06-06 2015-06-02 Trudell Medical International Oscillating positive expiratory pressure device
US9358417B2 (en) 2011-06-06 2016-06-07 Trudell Medical International Oscillating positive expiratory pressure device
US9180271B2 (en) 2012-03-05 2015-11-10 Hill-Rom Services Pte. Ltd. Respiratory therapy device having standard and oscillatory PEP with nebulizer
US9517315B2 (en) 2012-11-30 2016-12-13 Trudell Medical International Oscillating positive expiratory pressure device
US9795752B2 (en) 2012-12-03 2017-10-24 Mhs Care-Innovation, Llc Combination respiratory therapy device, system, and method
US9511202B1 (en) * 2012-12-04 2016-12-06 Mercury Enterprises, Inc. Breathing assistance device with nebulizer
US9849257B2 (en) 2013-08-22 2017-12-26 Trudell Medical International Oscillating positive respiratory pressure device
USD778429S1 (en) 2015-09-02 2017-02-07 Trudell Medical International Respiratory treatment device
USD780906S1 (en) 2015-09-02 2017-03-07 Trudell Medical International Respiratory treatment device
US9981106B2 (en) 2016-04-29 2018-05-29 Trudell Medical International Oscillating positive expiratory pressure device

Also Published As

Publication number Publication date Type
US6076519A (en) 2000-06-20 grant

Similar Documents

Publication Publication Date Title
US3490452A (en) Therapeutic face mask
US5713349A (en) Inhalation therapy
US5752506A (en) Ventilator system
US4444202A (en) Breathing exerciser
US6125844A (en) Portable oxygen based drug delivery system
US4809706A (en) Incentive inhalation spirometer apparatus
US6510846B1 (en) Sealed back pressure breathing device
US5752502A (en) General purpose aerosol inhalation apparatus
US6470882B1 (en) Pernasal application of aerosol medication
US7523752B2 (en) System and method of administering a pharmaceutical gas to a patient
US5813401A (en) Nebulizer automatic control valve
US20040084048A1 (en) High FIO2 oxygen mask with a sequential dilution feature and filter
US7870857B2 (en) Patient interface assemblies for use in ventilator systems to deliver medication to a patient
US6659100B2 (en) Sealed back pressure breathing device
US20080142019A1 (en) High flow therapy device utilizing a non-sealing respiratory interface and related methods
US7290541B2 (en) Aerosol delivery apparatus and method for pressure-assisted breathing systems
US6014972A (en) Dry drug particle delivery system and method for ventilator circuits
US6588421B1 (en) HME bypass system
US5904140A (en) Medical pacifier
US7347205B2 (en) Method for use with the pressure triggering of medical ventilators
US5701886A (en) Treatment non-rebreather assembly and method for delivering oxygen and medication
US7204245B2 (en) Aerosol enhancement device
US5000173A (en) Respiratory aid device
US5119807A (en) Pressurized medical ventilation system
US4261354A (en) Inhalator-breathing apparatus

Legal Events

Date Code Title Description
AS Assignment

Owner name: ETHEX INTERNATIONAL, INC., CALIFORNIA

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:JOHNSON, ROBERT J.;REEL/FRAME:006802/0739

Effective date: 19931210

FPAY Fee payment

Year of fee payment: 4

REMI Maintenance fee reminder mailed
LAPS Lapse for failure to pay maintenance fees
FP Expired due to failure to pay maintenance fee

Effective date: 20041105